Aqueous methacetin solutions labelled with 13C having propylene glycol as a solubilizer

ABSTRACT

An analysis method determines a functional parameter of an organ by measuring  13 CO 2  content in exhaled air of an individual to which a substrate has been administered. The reaction of the substrate in the body of the individual enriches the exhaled air with  13 CO 2 . The maximum reaction rate of the substrate in the body is determined via a change of the measured  13 CO 2  content in the exhaled air using zero-order enzyme kinetics. An aqueous methacetin solution having a pH greater than 7.0 is used in the analysis method. A face mask separates the exhaled air from inhaled air. The face mask is configured such that inhaled and exhaled air flows essentially completely through the face mask. Exhalation and inhalation valves in the face mask allow a flow of inhaled and exhaled air through the face mask. A diagnostic method is used to determine the functional parameters of the organ.

This application is a divisional of U.S. application Ser. No.11/993,817, which is the U.S. national stage of InternationalApplication No. PCT/DE2006/001086, filed Jun. 26, 2006, which claimspriority to German Application No. 10 2005 028 836.7 filed on Jun. 25,2005. The foregoing patent applications are incorporated herein byreference.

DESCRIPTION

The invention relates to an analysis method for determining a functionalparameter of an organ, to an aqueous methacetin solution suitable forthis analysis method, to the use of this methacetin solution, to arespiratory mask for use in an analysis method according to theinvention, and to a diagnostic method for determining a functionalparameter of an organ.

The determination of a functional parameter of an organ, in particularthe quantitative determination of liver function, is of great importancein many areas of medicine. Chronic liver diseases are widespread inEurope, with 8.9 million people affected by hepatitis C. As theirdisease progresses, these individuals or patients find themselves inmost cases under permanent medical care. In the therapy and managementof patients with chronic liver diseases, quantifying the liver functioncan greatly improve the therapy control, and assessment of liverfunction is crucial in ensuring that the correct therapeutic decisionsare made.

Partial liver resection is a common method used in surgery today. It isperformed as a segmental resection or hemihepatectomy along theanatomical margins. Extensive interventions in the parenchymatous organwere made possible by the development of a wide variety of operatingtechniques. The post-operative morbidity and mortality after liverfailure, however, is still a considerable problem, due to inadequateliver function capacity resulting from previously damaged liver tissueor from there being too little liver tissue remaining. Many of thesurgical procedures, however, have to be performed in previously damagedliver tissue, in most cases where the liver has been transformed bycirrhosis. It is therefore necessary to be able to determine thefunctional liver capacity of a patient before the partial liverresection, so as to ensure that patients who no longer have sufficientfunctional reserves of liver tissue are not subjected to what is forthem a high-risk operation or are not assigned to other treatmentmethods.

Assessment of liver function is of particular importance in livertransplantation, since here the organ function has to be assessedwithout delay and a treatment decision has to be made quickly. In manyclinical situations, it is also difficult to assess whether there is aparenchymatous disturbance or whether other causes are responsible forthe clinical symptoms presented by the patients. In summary, therefore,there is a great need for a genuinely quantitative liver function testfor broad application in medicine.

Efforts are therefore being made across the world to develop simpletests that allow prognostic statements to be made concerning thefunctional reserves of liver cell tissue. Conventional laboratoryparameters are very unreliable and therefore unsuitable for thispurpose. They are not sufficiently sensitive to permit reliableevaluation of the complex biological processes in the hepatocyte(biosynthesis, biotransformation, catabolism of xenobiotics, etc.) andof the changes in these processes in the presence of disease.

In addition, they are subject to a large number of external influencesand are distorted by these. For example, they are to some extentdistorted by the required therapeutic intervention, by replacement ofhuman plasma, clotting factors or albumin, and can thus not be used asliver function parameters. Many different liver function tests have beendescribed in the literature (Matsumoto, K., M. Suehiro, et al. (1987):“[¹³C]methacetin breath test for evaluation of liver damage.” Dig DisSci 32 (4): 344-8, 1987; Brockmoller, J. and I. Roots (1994):“Assessment of liver metabolic function. Clinical implications.” ClinPharmacokinet 27 (3): 216-48).

However, it has not hitherto been possible, with any test method, tomake valid and genuinely quantitative statements on liver function. Inall methods to date, it was possible only to make a significantdifferentiation between different disease groups with already clinicallydetectable signs. Consequently, in clinical practice, no liver functiontest is employed in routine diagnostics, since these tests do not affordany additional clinical benefit based on their present accuracy.

The ¹³C-methacetin breath test used hitherto, with an exclusively oraladministration of the substance, is a method which can distinguishbetween the liver function capacity of healthy subjects and that ofpatients with chronic hepatitis without cirrhosis and with cirrhosis inthe different Child-Pugh stages (Matsumoto, K., M. Suehiro, et al.(1987): “[¹³C]methacetin breath test for evaluation of liver damage.”Dig Dis Sci 32 (4): 344-8, 1987), but does not permit a genuinequantification.

The substance methacetin is demethylated to paracetamol in a rapidone-step reaction by the enzyme CYP1A2 in the liver, with CO₂subsequently being produced. By ¹³C-labeling of the methyl group bondedvia the ether bridge, ¹³CO₂ can then be measured in the exhaled air. Thefollowing formula (I) represents the structural formula of methacetin:

The aim of genuine quantification with an individual measurement resultcannot be achieved using the previous methods. There are two reasons forthis:

1. The basis for statements derived from a breath test is that the stepto be evaluated in the cascade of processes of absorption and metabolismhas to be the step that determines the reaction rate. In the previousmethods for evaluating the liver function (oral administration of thetest substance), however, the rate-determining step is in most cases theabsorption, not the conversion of the substrate in the liver.

2. To be able to make quantitative statements on the basis of an enzymesystem (in the present case: to be able to determine the maximum liverfunction capacity, that is to say the functional liver capacity), theenzyme system to be tested has to be fully utilized at least in theshort term. Only in this case does the reaction proceed independently ofthe substrate concentration.

For a genuine quantification, therefore, it is imperative to reachsubstrate surplus. If this is not achieved, the reaction rate isdirectly proportional to and therefore dependent on the substrateconcentration, which for its parts drops non-linearly. A quantitativestatement on functional capacity is impossible. In all studies usingoral test substances, no genuine quantification could therefore takeplace, because full enzyme utilization is not achieved with the previousmethods. This has the following causes:

1. When used orally, methacetin must first pass through the stomach andbe transported as far as the duodenum and the proximal jejunum in orderto be absorbed. Only then can the substance reach the liver by way ofthe portal vein. In principle, this process costs time and results indelayed and incomplete inundation in the liver. This is extremelyvariable and is influenced by numerous physiological and pathologicalconditions. For example, in cirrhosis of the liver, in which liverfunction tests could be used for staging and for therapy management, theintestinal transit and absorption is greatly changed (Castilla-Cortazar,I., J. Prieto, et al. (1997): “Impaired intestinal sugar transport incirrhotic rats: correction by low doses of insulin-like growth factorI”. Gastroenterology 113 (4): 1180-7). In the period following abdominaloperations too (e.g. liver resections or liver transplants), intestinalatony (paralytic ileus) means that no reliable statement can be made atall.

2. A sufficient dose of the test substance is necessary. With too low adose, as in most methods for carrying out the oral methacetin breathtest, full utilization of the enzyme system per se is not achieved.

It should also be noted that methacetin is extremely sparingly solublein water or in an aqueous buffer. It crystallizes out of a usuallyaqueous solution within a period of hours to days. Such a solution canbe used only, if indeed at all, for oral administrations of methacetin.Other administration forms are not possible.

Moreover, in the previous methods, the percentage recovery rate of theapplied dose (dose %/h) and the cumulative dose are analyzed at specifictimes or time intervals in order to determine the liver function. Thecalculation of the dose %/h does not absolutely define the reactedsubstrate quantities and also does not take account of the individualbodyweight of the patient. It is not possible in this way toindividualize and thus standardize the results in order to class themaximum functional liver capacity into a standard population.

The previous determination of the metabolized cumulative dose D_(kum)over a defined period of time is equally inexpressive in respect offunctional liver capacity. For a reliable statement concerning themaximum conversion of the enzyme system over time, said system wouldhave to be fully utilized over the entire period. For the reasonsmentioned above, this is not the case. Consequently, the presently usedcalculation of the cumulative dose cannot be used for quantifying thefunctional liver capacity.

To transfer the air exhaled by an individual into a measurement device,it is recommended to use a respiratory mask which is placed onto theface of the individual. For the subsequent reliable conduct of ananalysis method, it is critically important that the exhaled air issafely separated from the inhaled air and, in addition, that unforcedbreathing by the individual is permitted by a low airway resistance ofthe respiratory mask.

Various types of respiratory masks are in common use in medicine, inoccupational safety and also in diving. In medicine, this is the case inthe induction and performance of anesthesia or also for respiratorytherapy and noninvasive ventilation. Masks with a good matching shapeand a tight fit are preferred, and the required valves are fittedoutside the masks, in the tube systems or in the other connectedappliances.

Valves are installed in some masks used in occupational safety and alsoin masks used in diving, but the focus here lies in the delivery ofrespiratory gas and in the secure sealing of the system. High airwayresistance generally arises in these cases, with the result that, forexample, a medical test is needed to ensure suitability beforeoccupational use of such a system.

To analyze certain constituents in the exhaled air, it is necessary toseparate the respiratory gas path as close as possible to the site oforigin of the exhaled substances, i.e. as close as possible to thepulmonary alveoli. Otherwise, the inhaled air and the exhaled air mixtogether. Moreover, the separation must not cause any substantialincrease in airway resistance, especially not in the case of patientswhose pulmonary function is compromised for whatever reason. Theinhalation resistance specifically should not substantially increase,since the respiratory work or the supply of gas cannot be mechanicallyassisted as it is, for example, in anesthesia, ventilation, or in divingequipment or occupational safety equipment. Moreover, it is of greatimportance to establish, during the analysis, whether the respiratorymask is sitting tightly on the face or has possibly just been taken off.

The object of the invention is to make available a reliable analysismethod for determining a functional parameter of an organ of anindividual and also a corresponding diagnostic method, and to makeavailable a methacetin solution in which dissolved methacetin remainsstably dissolved over a period of weeks or months and can thus be usedas a substrate in the methods according to the invention.

This object is achieved by an analysis method for determining afunctional parameter of an organ of a human or animal individual.According to this analysis method, the ¹³CO2 content in the air exhaledby the individual is measured, the ¹³CO₂ in the body of the individualbeing formed enzymatically from a substrate that has been administeredbeforehand to the individual, and then being exhaled by the individual.The measurement of the ¹³CO2 content in the air exhaled by theindividual is carried out using a suitable measurement device. Themaximum reaction rate of the substrate in the body of the individual isdetermined via a change of the measured ¹³CO₂ content in the air exhaledby the individual using zero-order enzyme kinetics. The analysis methodaccording to the invention therefore proceeds from a consideration ofenzyme kinetics.

The functional parameter of an organ that is to be determined ispreferably the liver function capacity and/or the microcirculation inthe liver. Thus, the analysis method is suitable in particular forquantifying the functional liver capacity of the individual. Thefunction of the liver, as the central organ of metabolism, is extremelycomplex. Many biochemical synthesis and degradation processes take placein the liver. A common feature, however, is that almost all of themfunction on the basis of an enzymatic metabolism.

The ¹³CO₂/¹²CO₂ ratio in the air exhaled by the individual is preferablydetermined. This value can be used as the ¹³CO₂/¹²CO₂ ratio in theformula (1) below.

In a particularly preferred embodiment of the invention, the maximumreaction rate (LiMAx) is calculated through the converted quantity ofsubstrate per unit of time in μg/h/kg bodyweight at variable times atwhich the maximum value is reached, such that genuine quantification ofthe maximum functional liver capacity can be made. The calculation iscarried out according to the following formula (1), which describeszero-order enzyme kinetics:

$\begin{matrix}{{{Li}\;{MAx}} = {\frac{\left( {{\delta^{13}C_{imax}} - {\delta^{13}C_{10}}} \right) \cdot R_{PDB} \cdot P \cdot M}{KG}\left\lbrack {\mu\; g\text{/}h\text{/}{kg}} \right\rbrack}} & (1)\end{matrix}$

Here, δ¹³C is the difference between the ¹³CO₂/¹²CO₂ ratio of the sampleand the Pee Dee Belmite (PDB) standard in delta per mil, R_(PDB) is the¹³CO₂/¹²CO₂ ratio of the PDB standard (0.0112375), P is the CO₂production rate (300 mmol/h×surface area of body in m²), M is themolecular weight of the substrate, and KG is the actual bodyweight ofthe individual in kg.

In another preferred embodiment of the invention, it is not the¹³CO₂/¹²CO₂ ratio, but the absolute ¹³CO₂ content that is determined inthe air exhaled by the individual. This is possible, for example, bymeans of isotope-selective infrared spectroscopy. In the formula (1),the absolute ¹³CO₂ volume concentrations integrated over time are thenused directly instead of the ¹³CO₂/¹²CO₂ ratios, and it is thereforealso possible to omit the factors R_(PDB) and P and, consequently, thedependence of the merely generally estimated CO₂ production rate. The¹³CO₂ volume concentration represents the concentration of the ¹³CO₂ inthe whole of the exhaled air, that is to say that, in the preferred useof the ¹³CO₂ content in the air exhaled by the individual, the volume ofthe entire respiratory gas stream is determined in addition to the ¹³CO₂concentration. This also yields the rate of metabolism (μg/h/kg), thatis to say the converted quantity of substrate per unit of time,standardized to the bodyweight of the individual.

The formula (1) is simplified to the formula (2) when determining theabsolute ¹³CO₂ concentration:

$\begin{matrix}{{LiMAx} = {\frac{\int\limits_{t = t_{\max}}^{t = {t_{\max} + i}}{\left\lbrack {{}_{}^{}{}_{}^{}} \right\rbrack{{\mathbb{d}t} \cdot {\int\limits_{t = t_{\max}}^{t = {t_{\max} + i}}{\overset{.}{V}{{\mathbb{d}t} \cdot M}}}}}}{KG}\left\lbrack {\mu\; g\text{/}h\text{/}{kg}} \right\rbrack}} & (2)\end{matrix}$

Here, [¹³CO₂] is the absolute concentration of the ¹³CO₂ per unit ofvolume in the air exhaled by the individual, f7 is the volume per unitof time, t is the time, tmax is the time of maximum metabolism, i is thesmallest possible time resolution according to the measurement method, Mis the molecular weight of the substrate, and KG is the currentbodyweight of the individual in kg.

An infrared spectrometer is preferably used to spectrometer determinethe ¹³CO₂ content in the exhaled air, since ¹³CO2 has an absorption bandeasily separated in the infrared range.

In NDIRS measurement devices (NDIRS=nondispersive infraredspectroscopy), the water vapor contained in the exhaled air is removedbefore the measurement, advantageously by a humidity exchanger connectedupstream of the measurement device, in order to avoid undesiredabsorption of the water vapor in the infrared range. A particularlysuitable humidity exchanger is, for example, a Nafion humidityexchanger. However, other humidity exchangers that are able toeffectively dry the air exhaled by the individual are also similarlysuitable.

In isotope-selective determination of the absolute ¹³CO2 content in theair exhaled by an individual, this drying of the exhaled air to beanalyzed is preferably omitted, since the bands of the water vapor arenot superposed with the ¹³CO2 band or bands to be observed.

In a preferred embodiment of the invention, not only is the maximumreaction rate of the substrate in the body of the individual determined,but also the inundation time, that is to say the time necessary to reachthe maximum reaction rate.

The inundation time is preferably used to assess the microcirculation inthe liver, so as to be able to detect microcirculation disturbances.Assuming the quickest possible inundation by in particular intravenousbolus injection and substrate excess and the high first-pass effect ofmethacetin or another substrate, the hepatic microcirculation can beassessed particularly advantageously. The inundation time needed toreach the maximum reaction rate t_(vmax) is determined, said inundationtime lengthening in the presence of microcirculation disturbances, sincein this case the substrate inundation is not uniformly or completelydelayed in all areas of the liver. Liver perfusion can thus be assessed.

The microcirculation and the liver perfusion are preferably not justassessed in isolation, but also assigned to a standard population. To doso, the inundation time is standardized to a normal population takinginto account the bodyweight of the individual. The same applies also tothe maximum reaction rate. By the reference to the individualbodyweight, it is possible to eliminate an interindividual variabilityand thus achieve a standardization. Only in this way is it possible toclass the individual functional liver capacity into a comparisonpopulation. With the method according to the invention, it is not onlypossible to differentiate between limited liver function (e.g. inmanifest cirrhosis of the liver) and healthy liver performance; instead,as a result of the rapid and complete utilization of the enzyme system,very slight differences in the maximum reaction rate (functional livercapacity) can now be determined over a wide measurement range.

To be able to detect the time of the maximum reaction rate, it isnecessary to analyze the ¹³CO2/¹²CO2 ratio and the relative or absolute¹³CO₂ content in the exhaled air over time.

Therefore, samples of respiratory gas are preferably collecteddiscontinuously at defined times and are analyzed with a respiratory gasanalyzer (measurement device) according to one of the techniquesdescribed above. For example, the respiratory gas samples can becollected at the times 0 min and 2¹-, 5, 10, 15, 20, 30, 40, 50 and 60min after the application of the test substance (substrate). Thismeasurement method is also referred to as discontinuous offlinemeasurement. The measurement of the respiratory gas samples, that is tosay of the exhaled air to be analyzed, can be carried out directly whenthe samples are collected or after a delay time. In other words, thecollected samples of respiratory gas can be temporarily stored prior toa measurement, for example if no measurement device is immediatelyavailable for use.

It is ideal, and preferable, to perform a continuous analysis of theexhaled air using a respiratory gas analyzer as measurement device(online measurement).

The measurement preferably extends over a time interval in which theenzyme kinetics proceed or the shortest time interval within which areliable determination of the enzyme kinetics takes place. In diseasedindividuals, an analysis for a time interval of about 60 minutes isnecessary. In healthy individuals, in whom the maximum reaction rate ofthe substrate in the liver is reached after just a few minutes, theanalysis method can be terminated once the maximum reaction rate hasbeen reached, that is to say after a few minutes (for example 5minutes).

The continuous online measurement of the ¹³CO₂ content in the airexhaled by the individual results in particular in a considerable savingin time in the examination of healthy individuals since, in the offlinemeasurement, the respiratory samples are first of all collected andthereafter analyzed, such that early termination of the analysis methodis not really possible. In diseased individuals too, however, there isstill a distinct saving in time, since the result of the measurement isavailable immediately upon conclusion of the measurement, and forwardingto a laboratory, or a renewed intervention by the operator, is notneeded.

As a result of an increased time resolution in continuous onlinemeasurement compared to the discontinuous offline measurement, more datapoints are obtained, which results in greater precision of the analysisof the curves.

Since, in continuous online measurement, no respiratory gas bag has tobe inflated at set times, there is no dependency on the operator inrespect of said times; the data points can thus be assigned, with asignificantly reduced error, to a point in time within the proceedingenzyme kinetics.

The continuous online measurement is also preferred for the reason thatit permits fully automatic measurement, especially if, by suitablemeasures, the gas delivery (i.e. the correct fit of a respiratory maskon the face of the individual) is guaranteed.

The air exhaled by the individual is preferably collected at theindividual's face by means of a respiratory mask, in particular arespiratory mask having the features explained further below in thedescription, and is transferred from here through a tube or otherconnecting line into the measurement device, in order to then performthe analysis method.

In a particularly preferred embodiment of the invention, the substrateused is ¹³C-labeled methacetin. This ¹³C-methacetin has a molecularweight of 166.19 g/mol.

In the reaction of ¹³C-methacetin in the body of the individual, aliver-specific enzyme system is tested which, however, does not occur insuch great ratio that complete utilization of the enzyme could beachieved at any time. The cytochrome p-450 isoenzyme CYP1A2 is thereforesuitable. Only relatively few substances are metabolized by CYP1A2, suchthat the factors influencing and disturbing it are small. Nevertheless,it is to be regarded as representative of the liver function.

The substance methacetin is demethylated to paracetamol by CYP1A2 in arapid one-step reaction, with CO₂ then resulting. A rapid and completereaction is ensured by the high first-pass effect. ¹³C-methacetin isthus eminently suitable. By ¹³C-labeling of the methyl group bonded viathe ether bridge, ¹³CO₂ can then be measured in the exhaled air. Thiscan be done by analyzing the exhaled air using a suitable respiratorygas analyzer. Suitable methods for this purpose are, for example,isotope-selective nondispersive infrared spectroscopy orisotope-selective mass spectroscopy. With both methods, the measuredvalue provided is the difference of the ¹³CO2/¹²CO2 ratio of the sampleand the Pee Dee Belmite (PDB) standard in delta per mil (5¹³C).

The object of the invention is also achieved with an aqueous methacetinsolution. Accordingly, the pH value of the solution is set such that thesolution is basic, with a pH value of 7.5 to 9.5 and in particular of8.0 to 8.5 being particularly preferred. Thus, for example, a pH valueof 8.2 has proven particularly advantageous.

To better dissolve the methacetin, the methacetin solution preferablycontains a solubilizer.

Propylene glycol has particularly advantageous solubilizing properties,and it is at a concentration of preferably 10 to 100 mg/ml, morepreferably of 20 to 50 mg/ml, particularly preferably of 25 to 35 mg/ml,and very particularly preferably of 30 mg/ml, that said advantageoussolubilizing properties of the propylene glycol come to the fore.

In a preferred variant of the invention, the methacetin solution issterile and/or pyrogen-free, such that the methacetin solution can beadministered to a human or animal individual or patient without fear ofhealth-related complications.

The methacetin in the methacetin solution preferably has a concentrationof 0.2 to 0.6% (w/v), particularly preferably of 0.3 to 0.5%, and veryparticularly preferably of 0.4%. At this concentration, the methacetinin the methacetin solution according to the invention is readilysoluble. At lower concentrations, preferred in respect of solubility,the volume of the methacetin solution that has to be administered to atest individual increases significantly, which is undesirable. At ahigher methacetin concentration, by contrast, there is a danger of themethacetin precipitating or crystallizing out of the solution.

In order to advantageously use the methacetin solution for performing abreath test for determining functional parameters of an organ, thedissolved methacetin is preferably labeled with the carbon isotope ¹³C.This labeling is preferably restricted only to those areas of themolecule which are released as CO2 upon reaction in the body of anindividual. This is the methyl group shown at the left margin in formula(I). By limiting the ¹³C labeling to this methyl group, products of thebreakdown of methacetin other than CO2 have no labeling, such that thesebreakdown products do not interfere with measurements that are based onthe determination of the content of ¹³CO₂.

The invention also relates to the use of a methacetin solution accordingto the invention in an analysis method for determining the functionalparameter of an organ of a human or animal individual.

A further aspect of the invention is the use of a methacetin solutionaccording to the invention in an analytical or diagnostic method fordetermining the dynamic distribution of methacetin in an organ of anindividual by means of nuclear magnetic resonance spectroscopy (NMR) ormagnetic resonance therapy (MRT). Since ¹³C is NMR-active, it isrecommended to investigate the dynamic distribution of methacetin in theliver, for example, in order to be able to draw conclusions regardingliver damage. In such a method, dynamic processes in the liver can beinvestigated with relatively high time resolution (in the minute range).Liver areas not accessible to a through-flow of methacetin are onlyinadequately supplied, if at all, with other substances too, such that acorrelation to (partial) liver damage can be drawn in this way.

The object is also achieved by a respiratory mask for separating theexhaled air from the inhaled air of an individual, since such arespiratory mask is particularly suitable for conveying the air exhaledby an individual into a measurement device, which air is analyzed in thelatter in an analysis method according to the invention. Such arespiratory mask has a respiratory mask body and a gas cushion, whichextends around the respiratory mask body and is arranged between theface of the individual and the respiratory mask body during operation.

The gas cushion is filled with gas and permits a substantially gas-tightcontact between the face of the individual and the respiratory mask,which is arranged on the face of the individual. This gas-tight contactensures that inhaled air required by the individual and exhaled airexhaled by the individual is guided substantially completely through therespiratory mask. Inhaled air or exhaled air does not in practice flowunder the gas cushion into the area surrounded by the respiratory mask,but only through inhalation and exhalation valves, specifically at leastone exhalation valve and at least one inhalation valve that areintegrated directly into the respiratory mask.

The basic shape of the respiratory mask body is preferably produced indifferent sizes to match the size of face of the individual who is towear the mask (e.g. for children, small adults, medium-sized adults,large adults, very large adults, etc.), so as to permit a secure fit ofthe respiratory mask on a large number of face shapes.

The gas cushion preferably has a valve, which can have a Luer connectorfor example, or a similar closure piece. By means of this valve orclosure piece, the degree of filling of the gas cushion can be adjustedin order to further optimize the secure fit of the respiratory mask onthe face of the individual.

Air in particular is recommended as the gas with which the gas cushionis filled. However, other gases can equally be used as the gas forfilling the gas cushion, but these gases should be noncombustible andnontoxic, so as to minimize the risk of injury to the individual wearingthe mask.

The solid plastic housing of the respiratory mask body additionallycomprises a solid, conical attachment for an oxygen tube, so as to beable, when necessary, to supply the individual wearing the maskadditionally with oxygen or other added gas mixtures.

In a preferred embodiment of the invention, the inhalation valve andexhalation valve are installed fixedly in the respiratory mask body.

In an alternative embodiment of the invention, the valves can beseparately removed from the respiratory mask body and are clipped into amatching conical fixture in the respiratory mask body, as a result ofwhich a gas-tight connection is established between theinhalation/exhalation valve and the respiratory mask body.

The inhalation and exhalation valves are preferably composed of a thinand flexible, but sufficiently stiff membrane that coversthrough-openings formed in the valve for the through-flow of gas or air.The membrane can preferably be made of silicone, but can also be made ofother materials that satisfy said criteria.

For conveying the separated exhaled air to an analysis or measurementdevice, for example via a special tube, the exhalation valve preferablyhas an attachment for carrying off the separated exhaled air.

To ensure that the separated exhaled air is carried off from theexhalation valve in a uniform manner, the attachment for carrying offthe exhaled air is particularly preferably arranged centrally on theexhalation valve.

The attachment is preferably a conical attachment with an internaldiameter of 20 to 30 mm at its narrower opening, an internal diameter of22 mm being particularly preferred. Such a (standardized) attachmentpermits uncomplicated connection of a tube or other withdrawal device tothe attachment of the exhalation valve.

The main body of the respiratory mask preferably has a securing devicefor securing at least one holding element, by means of which therespiratory mask can be securely held on the face of the individual. Thesecuring device can, for example, be a hole that is suitably sealed offto ensure that no air passes through the hole into the area surroundedby the respiratory mask. The securing device is advantageously connectedonly to the outside wall of the respiratory mask body and has the shapeof a ring, a nipple or an eyelet. The securing device can, for example,be injection molded onto the respiratory mask body.

The holding element is preferably a rubber band, the length of which canbe varied if appropriate in order to ensure a secure fit of therespiratory mask on the face of the individual. A rubber band forholding the respiratory mask is fitted particularly preferably in eachcase in the mouth area and nose area.

A respiratory mask with the features discussed above is particularlysuitable for use in an analysis method or in a method for determiningthe functional parameter of an organ of a human or animal individual.

A pressure sensor is preferably integrated into the gas cushion and isconnected via a cable to a plug connection in the area of the attachmenton the exhalation valve. By means of this pressure sensor, it ispossible to reliably detect whether the respiratory mask is fitted inplace or not. The contact pressure provided by the rubber bands leads toan increase in pressure in the air cushion. By means of this change inpressure, and the time profile, it is possible to determine the times atwhich the respiratory mask is fitted tightly in place. Similarly,removal of the respiratory mask, for example by the individual, can beautomatically registered. This control possibility afforded by theintegrated pressure sensor is also conceivable in many situations and inother respiratory masks with air cushions (e.g. in intensive caremedicine).

The data measured by the pressure sensor integrated in the respiratorymask can be evaluated by an interconnected online measurement device,that is to say a measurement device suitable for a continuous onlinemeasurement.

The object of the invention is also achieved by use of the respiratorymask according to the invention in an analysis method according to theinvention, since the respiratory mask ensures a safe and reliableprovision of the exhaled air that is to be analyzed at the measurementdevice, such that the analysis method can be reliably performed.

The object of the invention is also achieved by a diagnostic method fordetermining the functional parameter of an organ of a human or animalindividual or patient. This method involves an intravenous injection ofa ¹³C-labeled methacetin solution according to the invention into thebody of the individual, and thereafter an analysis of the relativeand/or absolute ¹³CO₂ content in the air exhaled by the patient, usingan analysis method according to the invention that has already beenexplained above.

The functional parameter of an organ to be determined is preferably theliver function capacity and/or the microcirculation in the liver.

The rapid substrate inundation required for the enzyme-kineticevaluation is ensured by the fact that ¹³C methacetin is administeredintravenously in a bolus. The intravenous bolus injection ensures animmediate and complete substrate inundation in the liver. The absorptionof the test substance ¹³C-methacetin is no longer the step thatdetermines the reaction rate. With the preferred dose of 2 mg methacetinper kg bodyweight, a temporary enzyme utilization is also permitted inpatients with a healthy liver by a short-term substrate excess. Thispermits the actual quantitative expressiveness, since zero-order enzymekinetics are achieved, and only this permits a statement concerning themaximum functional capacity of an enzyme system.

The stable intravenous administration of the sparingly water-soluble¹³C-methacetin in a concentration sufficient for bolus injection ispreferably achieved by the ¹³C-methacetin being dissolved in aconcentration of 4 mg/ml in water for injection and the addition of 30mg propylene glycol per ml and the setting of a basic pH value of 8.5.The solution is prepared sterile and pyrogen-free, and its osmolarity isset such that its administration to the individual to be tested can beperformed without difficulty through a peripheral vein.

BRIEF DESCRIPTION OF THE DRAWINGS

The invention will be explained in more detail on the basis of thefollowing figures and of an illustrative embodiment, without theseexplanations limiting the scope of protection of the invention.

FIG. 1 is a graph showing the mean delta-over-baseline values over timein a liver function study on patients who had undergone a partial liverresection;

FIG. 2 is a graph showing the actual functional mean liver capacities(LiMAx), calculated from the data in FIG. 1, as a function of time;

FIG. 3 is a graph showing the mean inundation time of the substrate¹³C-methacetin in the liver as a function of time, for determining themicrocirculation in the liver;

FIG. 4 is a side view of an illustrative embodiment of a respiratorymask according to the invention, and

FIG. 5 is a plan view of the respiratory mask from FIG. 4.

FIGS. 1 to 3 will be explained in more detail on the basis of thefollowing illustrative embodiment.

EXAMPLE 1

In the context of a prospective study, a method, which is discussed inmore detail below, was used to evaluate liver function before and afterpartial liver resection in a number of patients:

-   1. Method and means for enzyme-kinetic quantification of liver    function capacity and for assessment of microcirculation    disturbances of the liver, characterized in that    -   a) A special intravenous ready-to-use solution of ¹³C-labeled        methacetin is injected intravenously in a sufficient dose to        ensure rapid inundation of the substance in the liver, with        substrate surplus on the metabolizing enzyme system.    -   b) By analyzing the ¹³CO2/¹²CO₂ ratio in the exhaled air over a        period of time of one hour following injection, the maximum        reaction rate of the ¹³C-labeled methacetin is determined using        zero-order enzyme kinetics.    -   c) By standardizing to the individual bodyweight, comparability        with a normal population is provided.    -   d) Microcirculation disturbances in the liver can be assessed by        determining the inundation time until the maximum reaction rate        is reached.-   2. Method according to point 1, characterized in that a ¹³C-labeled    methacetin solution is used in a concentration of 0.4%.-   3. Method according to points 1 and 2, characterized in that the    ¹³C-labeled methacetin solution contains 30 mg/ml of propylene    glycol for stabilization, and the pH value is basic.-   4. Method according to points 1 to 3, characterized in that the    ¹³C-labeled methacetin solution is sterile and pyrogen-free.-   5. Method according to points 1 to 4, characterized in that the    ¹³CO2/¹²CO₂ ratio is ideally determined continuously, or otherwise    at the defined times of 0 min and 2¹-, 5, 10, 15, 20, 30, 40, 50 and    60 min after injection of the ¹³C-labeled methacetin.

From the prospective study, FIG. 1 shows the curves of the meandelta-over-baseline (DOB) values of the ¹³CO2/¹²CO2 ratio in the airexhaled by the patients at the individual measurement times, plottedover time.

In the pre-operative stage, where there is a normal and maximumfunctional liver capacity, the curve rises steeply, then falls againafter the maximum value is reached. After partial liver resection, thecurve changes drastically on post-operative day 1 (POD1) to saturationkinetics with markedly reduced maximum function. As liver regenerationincreases after the partial liver resection, the curve changes backagain toward the pre-operative curve (POD3-10).

The actual functional liver capacity calculated from this in 1.1 g/h/kgis shown in FIG. 2. On POD1, the maximum functional liver capacity(LiMAx) falls from 301±24 1.1 g/h/kg to 141±13 1.1 g/h/kg, thereafterslowly regenerating back to a value of 249±17 1.1 g/h/kg onpost-operative day 10 (POD10).

The analysis of the microcirculation, represented in FIG. 3, shows amarked disturbance after the partial liver resection, in parallel with aprolongation of the inundation time (t-vmax) from 11.9±2.17 min to53.5±7.51 min, which subsequently recovers again.

FIG. 4 shows an illustrative embodiment of a respiratory mask 1according to the invention, which mask is particularly suitable forintroducing the air exhaled by an individual into a measurement devicefor carrying out an analysis method according to the invention. Therespiratory mask 1 is a respiratory mask to be placed centrally over theface.

The respiratory mask 1 has a housing 2 serving as the main body of therespiratory mask, and an air cushion 3 serving as a gas cushion which,on the side of the respiratory mask 1 directed downward in FIG. 4,extends all round the housing 2. During the use of the respiratory mask1, this side is directed toward the face of the individual wearing therespiratory mask 1.

The housing 2 of the respiratory mask 1 is made of a firm plastic. Thebasic shape of the housing can be configured in different ways to ensurethat individuals with different shapes of faces can apply a respiratorymask 1 that provides the best possible fit.

Two inhalation valves 4 are arranged at the sides of the upper end ofthe respiratory mask 1, which represents the nose area N of therespiratory mask 1, only one of these inhalation valves being seen inFIG. 4. Air flows through through-openings 40 formed in these inhalationvalves 4 and into the space between the respiratory mask 1 and the faceof the individual wearing the respiratory mask 1, when the individualbreathes in.

An exhalation valve 5 is arranged on the front of the respiratory mask1, which is arranged at the top in FIG. 4. Air exhaled by the individualflows through through-openings 50 arranged in the exhalation valve 5when the individual is wearing the respiratory mask 1 correctly andbreathes out. Arranged at the center of this exhalation valve 5, thereis a minimally conical attachment 6, which has an internal diameter of22 mm. Air exhaled by the individual is carried off through thisattachment 6. For this purpose, it is possible to use a tube (not shownhere) connected to the attachment 6.

By virtue of the specific arrangement of the inhalation valves 4, on theone hand, and of the exhalation valve 5, on the other hand, and of theconfiguration of the inhalation valves 4 and of the exhalation valve 5,it is possible to ensure separation of the inhaled air from the exhaledair of the individual wearing the respiratory mask 1. In addition, themixing volumes and dead volumes in the respiratory mask are minimized bythe arrangement of the inhalation valves 4 and of the exhalation valve5.

The housing 2 further comprises a conical gas attachment 7 through whichoxygen or a gas mixture can, if necessary, be introduced into the spacebetween the respiratory mask 1 and the face of the individual wearingthe respiratory mask 1. In this way, it is possible, for example, toprovide an additional supply of oxygen to the individual wearing therespiratory mask 1.

A rubber band (not shown in FIG. 4) is secured on holders 8 serving assecuring elements, which can be in the form of eyelets or nipples, forexample, this band ensuring a secure hold of the respiratory mask 1 onthe face of the individual wearing the mask. Instead of a rubber band,other holding means could also be used. The holders 8 are arranged ineach case in pairs in the nose area N at the top end and in the moutharea M at the bottom end of the respiratory mask 1.

The air cushion 3 of the respiratory mask 1 has a valve 9 arranged inthe mouth area M of the respiratory mask 1 with a Luer connector throughwhich the quantity of air in the air cushion 3 can be regulated. Thispossibility of adaptation allows the respiratory mask 1 to be optimallyadapted to the shape of the face of the individual wearing therespiratory mask 1.

A pressure sensor 10 is also integrated into the air cushion 3 in orderto allow the pressure in the air cushion 3 to be measured. For thispurpose, a cable connection 11 arranged on the front of the mask housingextends from the pressure sensor 10 to the exhalation valve 5. In thearea of the exhalation valve 5 and of the attachment 6 mounted on theexhalation valve, the cable connection 11 has a plug connection 12 ontowhich a further cable connection for controlling or reading the pressuresensor can be attached.

By means of the pressure sensor 10, it is possible to detect whether therespiratory mask 1 is sitting on the face of an individual or not. Thecontact pressure afforded by the rubber bands leads to a pressureincrease in the air cushion 3. Based on this change in pressure and onthe pressure profile over the course of time, it is possible todetermine the times at which the respiratory mask 1 is firmly fitted inplace. Moreover, an (undesired) removal of the respiratory mask by theindividual can be automatically registered. This control possibility viathe pressure sensor 10 integrated into the air cushion 3 is alsoconceivable in many situations and in other respiratory masks with aircushions (e.g. in intensive care medicine).

FIG. 5 shows a top view of the front of the respiratory mask 1 from FIG.4. For an explanation of the respiratory mask 1, reference is made tothe same reference numbers for the elements already discussed in FIG. 4.In a view complementing that of FIG. 4, FIG. 5 clearly illustrates thelateral arrangement of the exhalation valves 4 and the pairedarrangement of the holders 8 in the nose area N and in the mouth area Mof the respiratory mask 1.

What claimed is:
 1. An aqueous methacetin solution, wherein themethacetin is labelled with the carbon isotope ¹³C, wherein the pH valueof the solution is higher than 7.0 and lower than or equal to 9.5,wherein the methacetin has a concentration of 0.2 to 0.6% (w/v) andwherein the methacetin solution contains propylene glycol in aconcentration of 10 to 100 mg/ml as solubilizer that promotes thedissolution of methacetin.
 2. The aqueous methacetin solution accordingto claim 1, wherein the pH value of the solution is 7.5 to 9.5.
 3. Theaqueous methacetin solution according to claim 1, wherein the pH valueof the solution is 8.0 to 8.5.
 4. The aqueous methacetin solutionaccording to claim 1, wherein the concentration of the propylene glycolis 20 to 50 mg/ml.
 5. The aqueous methacetin solution according to claim1, wherein the concentration of the propylene glycol is 25 to 35 mg/ml.6. The aqueous methacetin solution according to claim 1, wherein themethacetin solution is at least one of sterile and pyrogen-free.
 7. Theaqueous methacetin solution according to claim 1, wherein the methacetinsolution has a concentration of 0.3 to 0.5% (w/v) methacetin.
 8. Theaqueous methacetin solution according to claim 1, wherein the methacetinsolution has a concentration of 0.4% (w/v) methacetin.
 9. The aqueousmethacetin solution according to claim 2, wherein the methacetinsolution has a concentration of 0.4% (w/v) methacetin.
 10. The aqueousmethacetin solution according to claim 3, wherein the methacetinsolution has a concentration of 0.4% (w/v) methacetin.
 11. The aqueousmethacetin solution according to claim 4, wherein the methacetinsolution has a concentration of 0.4% (w/v) methacetin.
 12. The aqueousmethacetin solution according to claim 5, wherein the methacetinsolution has a concentration of 0.4% (w/v) methacetin.
 13. The aqueousmethacetin solution according to claim 6, wherein the methacetinsolution has a concentration of 0.4% (w/v) methacetin.
 14. The aqueousmethacetin solution according to claim 7, wherein the methacetinsolution has a concentration of 0.4% (w/v) methacetin.